|Publication number||US7998107 B2|
|Application number||US 10/253,034|
|Publication date||Aug 16, 2011|
|Priority date||Sep 24, 2002|
|Also published as||CA2503484A1, CA2503484C, EP1545648A1, EP1545648B1, US8157787, US20040059284, US20120004601, WO2004028592A1|
|Publication number||10253034, 253034, US 7998107 B2, US 7998107B2, US-B2-7998107, US7998107 B2, US7998107B2|
|Inventors||John E. Nash, Gregory Walters, Stephen Heiman, Jim Barnitz, Pete Fatone|
|Original Assignee||Kensey Nash Corporation|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (18), Referenced by (3), Classifications (6), Legal Events (2)|
|External Links: USPTO, USPTO Assignment, Espacenet|
1. Field of the Invention
The invention generally relates to medical devices and procedures where fluids preferably are simultaneously infused and aspirated from the patient. The invention more particularly concerns a multi-use, or preferably a single-use pumping system, to infuse and aspirate liquids to and from a surgical site through a catheter, conduit or tube.
2. Description of Related Art
The use of pumping mechanisms to flush debris created during diagnostic and therapeutic procedures is not new, see for example U.S. Pat. No. 6,258,061 (Drasler), and U.S. Pat. No. 5,879,361 (Nash). These inventions describe using a catheter for clearing an occluded blood vessel, by using either a rotating impact head, coupled with a flushing mechanism (Nash) or using high pressure jets of fluid to clear the thrombus (Drasler).
Nash discloses the use of peristaltic pumps as the infusion and extraction pumps (Nash). Peristaltic pumps have a number of attributes that account for their widespread use in medical applications. The pumps are accurate in metering flow over a range of pressures. The maximum and minimum variations in flow rate during a pump cycle do not vary too greatly from the mean flow rate. The fluid pathway (e.g., a tube) of the pumps is easily sterilized and visible. When not in operation, there is very little if any leakage through the peristaltic pump head.
On the other hand, peristaltic pumps are relatively energy inefficient, thereby requiring AC power or large batteries as their power supply. In fact, the pumping system that uses such pumps is usually sufficiently large that it will not fit within the confines of the “sterile field” of the operating room. Thus, such a pump system typically is located at a remote region of the operating room, distant from the doctor, who must then direct another person to actually operate, or at least monitor, the pump system.
Drasler discloses the use of jets to emulsify the thrombus in the blood vessel. The high pressure jets as described are generated “with a positive displacement pump, such as a piston pump . . . ” which is designed to be disposable for sanitary reasons (Drasler). The pump can operate under pulsatile or steady flow. The invention described by Drasler may allow the fluid to exhaust by directing the spray of the catheter inlet back towards the exhaust outlet of the catheter, or alternatively “a vacuum pump to provide for removal of the fragmented thrombus or tissue, or a roller pump may be used to accomplish a similar effect.”
The Drasler inventions pertain to high pressure applications, such as cutting and emulsifying thrombi using liquid jets. When the medical intervention pertains to other treatments such as infusion of a diagnostic agent or a therapy, however, such single cylinder reciprocating pumps, by their design, result in large variations in instantaneous flow rate during a pump cycle. The fluctuations in the instantaneous flow rate range from a minimum flow rate of zero to a maximum that is a number of times greater than the mean flow rate. The fluctuating flow rate has a pronounced impact on the pressure in the aspiration.
The variations in instantaneous flow rate as a result of the back and forth motion of the pump piston require the liquid in the conduit connecting the patient to the pump to be accelerated during increasing flow, and decelerated during decreasing flow. When aspirating fluids, the force required to accelerate the flow in the conduit results in a decreased pressure at the entrance to the pump. The variations in flow rate also increase the instantaneous frictional losses in the catheter because the frictional losses are related to the square of the flow's velocity. The frictional losses at peak instantaneous flows are substantially higher than the losses associated with a steady flow at the mean flow rate. The force required to overcome the increased losses also results in a lower pressure at the pump entrance.
Both of the above effects are particularly troublesome in aspiration pumps since the minimum pressure at the pump is limited to the liquid's vapor pressure. If pressure falls to the liquid's vapor pressure, cavitation will occur (as the liquid boils) and aspiration will be impeded. Specifically, the evolving of vapor will render the actual extraction rate of liquid indeterminate. Further, if the system were to be shut off at that point, it is at least theoretically possible for an air bubble to be pushed back up the catheter into the patient, for example, if the aspiration pathway flow is reversed due to the introduction of drugs or contrast media, via activation of an injection port on a guide connector branch.
Another drawback associated with the reciprocating pump is leakage through the pump when it is stopped. The leakage occurs in the direction of flow and is due to the arrangement of the check-valves within the pump, which allow virtually unrestricted flow only in the intended direction. This drawback becomes problematic when the aspiration conduit is located in an elevated pressure environment such as an artery or the aspiration conduit is used as a pathway to introduce medication or other liquids when aspiration is stopped. Specifically, the arterial blood pressure can be sufficient to cause bleeding through the aspiration conduit, through the aspiration pump and into the aspiration or extraction bag.
The present invention addresses and solves these and other shortcomings of the prior art.
In spite of these inherent limitations of reciprocating-type pumps for medical applications, the efficiency and economics of such pumps are too attractive to ignore. Thus, it is an object of the present invention to provide an efficient and low cost substitute for peristaltic pumps in infusing and evacuating a fluid through a patient during a medical procedure on a living being.
It is an object of the present invention to provide infusion/evacuation pumps that are sufficiently compact as to be easily confined within the sanitized zone of a hospital operating room.
It is an object of the present invention to provide an infusion/evacuation pump whose economics are such as to justify disposing of the pump unit after just a single use.
It is an object of the present invention to provide a reciprocating type pump with a means for damping out the fluctuations in the aspiration pressure.
It is an object of the present invention to provide a means for preventing backflow into the aspiration pumping system.
It is an object of the present invention to provide a means for visually inspecting for air bubbles in the fluid pathway, particularly in the infusion fluid path.
It is an object of the present invention to provide a pumping system that is self-priming.
It is an object of the present invention to temporarily cease normal forward fluid flow through the fluid circuit, and to close off the aspiration path at a point beyond or after the catheter so that a diagnostic or therapeutic agent can be injected into the patient by way of an injection port in the catheter.
The pumping system of the present invention fulfills these and other objectives. Specifically, the pumping system of the invention utilizes non-peristaltic-type positive displacement pumps such as reciprocating pumps for flushing and extracting fluid through a catheter to clear debris. The invention furthermore features flow control devices such as a pulse damper and a shut-off valve, and a controller to manage the process. The combination of these features yields an infusion/aspiration circuit with all the desired attributes, including high efficiency, low cost and compact size.
Other objects and many of the attendant advantages of this invention will readily be appreciated as the same becomes better understood by reference to the following detailed description when considered in connection with the accompanying drawings wherein:
The objective of the invention is an infusion/aspiration pumping system that is compatible with the needs of a compact, single-use medical device for use in diagnostic and therapeutic treatments. The terms “aspiration” and “extraction” as used herein, are essentially synonymous. In a preferred embodiment, the system is suitable for use as a single-use device due to the incorporation of inexpensive non-peristaltic-type pumps, such as single cylinder reciprocating pumps, used in conjunction with other fluid control elements, to achieve flow attributes similar to that of a peristaltic pump design, yet at a much reduced cost and size. See
The pumping system (see
Again, one of the problems with reciprocating-type pumps is the variation or fluctuation in the pressure and flow rate of the medium being pumped, which often is undesirable in a medical intervention such as a catheterization. Thus, up to now, peristaltic pumps have been preferred for such procedures. The present invention addresses the fluctuating flow shortcoming of the single cylinder reciprocating pump by incorporating a compliant element (e.g., diaphragm 30, or damper spring 40 and damper piston 42, or elastomeric conduit 44, as shown in
Recall the other problem with reciprocating pumps, i.e., the leakage problem. Again, when the system is de-energized and the pumps are stopped, there is still an open path for fluid in the forward direction through the fluid circuit. Thus, in an arterial intervention where an intra-arterial catheter is attached to the pump system, the patient's blood pressure could cause the patient to bleed continuously through the aspiration side of the circuit. A preferred embodiment solves the leakage problem of reciprocating pumps by adding a shut-off valve 38 or 51 (as shown in
In a preferred embodiment, such as that illustrated in
In another embodiment, namely that illustrated by
The combination of a single cylinder reciprocating pump, pulse damper and shut-off valve yield an aspiration circuit with all the desired attributes including high efficiency, low cost and compact size.
For an infusion pumping circuit, single cylinder reciprocating pumps provide an attractive option with the exception of not being able to visually inspect the fluid pathway of the pump. Infusion devices that are used in the arterial or venous system need to provide protection against accidental air infusion. An effective and inexpensive means of protection is visual inspection of the fluid pathway prior to and during infusion.
A reciprocating pump consists essentially of a piston moving back and forth in a cylinder and two one-way valves that control flow into and out of the cylinder. An embodiment of the present invention mitigates the inspection problem by providing a transparent viewport 20 (as shown in
Referring again to
Unlike many of the prior peristaltic-based pumping systems, the infusion 64 and aspiration pumps 80 of the present invention may be arranged in a single housing 23, along with the necessary tubing 84, 85 and valves 66, 68 (referring to
The reciprocating, aspiration pump 80 as shown in
In use, the flexible infusion tubing 84 is connected to the source of fluid e.g., the reservoir bag 62, to be injected, generally located approximately two feet above the infusion pump 64 to provide some positive head pressure to the pump. The outlet from the pump 64 is connected via conduit of flexible infusion tubing 84 to a means of injecting the fluid within the body, such as a flush catheter 70, which may be inserted 71 through a guide connector branch 74 into the inner diameter of the guide catheter 72, ultimately extending out of the end of the guide catheter 72 and into the procedure site (e.g., saphenous vein graft, carotid, etc.)
The aspiration pump 80 and the infusion pump 64 may contain a mechanism to allow the determination of the speed of the pump, such as an optical sensor to detect light reflected from a reflective surface of the rotating motor shaft, or alternatively, a sensor to detect fluctuating voltage, which is proportional to the speed of rotation of the shaft, or any other means of detecting pump rotation. In this manner, a control system may be utilized to monitor, maintain or alter the speed of the pumps, or alternatively activate an alarm if needed, e.g., in the event of a stalled motor.
There will be instantaneous speed variations of the pumps in response to unusual events or flow conditions. Unlike the peristaltic pumps, the positive displacement pumps are in intimate contact with the fluid, and are intended to be sized to provide sufficient flow to meet the system requirements. A blocked catheter will cause the pumps to stall and stop pumping until the blockage is cleared. This feature precludes the need for a pressure sensor as is required on the peristaltic system, because the pumps are not powerful enough to cause a significant and possibly dangerous pressure without stalling. Conversely, if the pumped fluid changes to gas, from liquid, the pumps will speed up significantly due to the greatly reduced load. Therefore, a control system is very adaptable to these embodiments.
The pumps' sensitivity to load variations is also helpful during the priming process. While air is being cleared through the pumps ahead of the liquid, the pumps will run relatively fast, then slow down significantly when the liquid has reached the pumping cylinders. The speed variation is detectable and can be used to signal to the operator that the pump is primed with liquid. The same speed variation would occur in reverse if a primed system experienced a large leak, resulting in an ingestion of air, causing the pumps to speed up as previously discussed, this condition can be detected and used to initiate an alarm, for example.
The use of a typical embodiment of the pumping system of the present invention will now be described.
Starting the Saline Infusion
After priming the pumps 64,80, or more preferably relying on the pumps 64,80 self priming capabilities, the saline reservoir bag 62 is located in an elevated position to avoid entraining air in the system, and the flush catheter 70 is now inserted onto the guidewire by techniques known in the art. This attachment procedure has the potential to trap a small air bubble at the tip, just inside the flush catheter 70. In this case, the fact that there is an open flow path through the infusion pump 64 serves to create a positive drip through the catheter 70 and expel the air bubble. The flush catheter 70 is now slid along the guidewire, and inside the guide catheter 72 to the lesion site (via guide connector branch 74). The pump process begins with the aspiration pump 80 running first for a set time period to establish a suction pressure prior to the infusion pump 64 turning on. The infusion pump 64 turns on at a flow rate significantly less than that of the aspiration pump, to assure that debris is not forced distal of the procedure site, rather than into the guide catheter 72.
In yet another embodiment, a distal balloon (not shown) may be used to create an area which may be vigorously flushed without allowing any debris to travel in the distal direction. Additionally, aspirating more fluid than is infused may keep debris from backing up into the artery (etc.) in the proximal direction.
Injecting the Contrast Medium
To inject the contrast medium, the flow of saline from the reservoir bag 62 is halted and the extraction side shut-off valve 76 is closed. Using an automated control system, these steps can be carried out nearly simultaneously. The syringe (not shown) containing the contrast medium is purged of air, and inserted into the injection port 73 of guide connector branch 74 located at the proximal end of the guide catheter 72. The plunger of the syringe is depressed, thereby injecting the contrast medium into the guide connector branch 74. Note that this injection port is in a direct flow path with the extraction side 75 of the guide connector branch 74. Thus, the shut-off valve 76 should be in the “closed” position; otherwise, the relatively low resistance offered by the extraction side 75 of the guide connector branch 74 compared to the “patient” side 77 of the guide connector branch 74, will likely cause most of the contrast medium to flow straight out of the guide connector branch 74, ultimately ending up in the extraction bag 82, rather than in the patient, where it is desired. When injection is complete, the syringe may either be left in the guide connector branch 74, or it may be withdrawn. When the contrast has diffused sufficiently to where its visualization assistance is needed, the pumping system may be re-energized in the same sequence as described previously.
When the medical diagnostic or therapeutic treatment is complete, the pumps are de-energized, starting first with the infusate pump 64. The extraction side shut-off valve 76 is closed. The catheter 70 is withdrawn from the patient's body. The saline solution is drained or pumped into the extraction bag 82, clearing the lines. The liquid flow circuit is then disassembled, and the pump system may be discarded. Components that are to be re-used, if any, are cleaned and sterilized.
Thus since the invention disclosed herein may be embodied in other specific forms without departing from the spirit or general characteristics thereof, some of which forms have been indicated, the embodiments described herein are to be considered in all respects illustrative and not restrictive, by applying current or future knowledge. The scope of the invention is to be indicated by the appended claims, rather than by the foregoing description, and all changes which come within the meaning and range of equivalency of the claims are intended to be embraced therein.
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|U.S. Classification||604/35, 604/43|
|Cooperative Classification||A61M1/0035, A61M1/0058|
|Dec 26, 2002||AS||Assignment|
Owner name: KENSEY NASH CORPORATION, PENNSYLVANIA
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:NASH, JOHN E.;WALTERS, GREGORY;HEIMAN, STEPHEN;AND OTHERS;REEL/FRAME:013623/0788
Effective date: 20021226
|Feb 4, 2015||FPAY||Fee payment|
Year of fee payment: 4